Photoacoustic apparatus

ABSTRACT

In a photoacoustic apparatus, a light source irradiates an inspection target with pulsed light; a detector detects acoustic waves generated in the inspection target due to interaction of the pulsed light with the inspection target, and outputs detection signals corresponding to the detected acoustic waves; a light-quantity measurement unit measures the quantity of the light output from the light source; and a signal processor obtains information on an inside of the inspection target by using the detection signals output from the detector. The signal processor also corrects intensities of the detection signals so as to suppress variations in intensities of the detection signals caused by a temporal change in the quantity of the light.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a Continuation of co-pending U.S. patent applicationSer. No. 14/946,636 filed Nov. 19, 2015, which is a Continuation ofprevious U.S. patent application No. 12/908,232 filed Oct. 20, 2010, nowU.S. Pat. No. 9,2266,62 issued Jan. 5, 2016, which claims prioritybenefit from International Application No. PCT/JP2009/068614, filed Oct.29, 2009. The disclosures of the above-named applications and patent arehereby incorporated by reference herein in their entirety.

TECHNICAL FIELD

The present invention relates to a photoacoustic apparatus whichirradiates an inspection target with light so that photoacoustic wavesare generated and which receives the photoacoustic waves.

BACKGROUND ART

An optical imaging apparatus which irradiates a living body with lightand which images information on an inside of the living body obtained inaccordance with the incident light has been actively researched in amedical field. An example of such an optical imaging technique includesphotoacoustic tomography (PAT). In photoacoustic tomography, a livingbody is irradiated with pulsed light generated from a light source sothat acoustic waves generated from body tissues which absorb energy ofthe pulsed light which is propagated and dispersed in the living bodyare detected. One example of such a technique is described in U.S. Pat.No. 5,840,023 entitled “Optoacoustic Imaging for Medical Diagnosis”(hereafter “Patent Literature 1”). Specifically, elastic waves, that is,photoacoustic waves, generated when a detection target absorbs theirradiated light energy and therefore is momentarily expanded arereceived by a transducer by utilizing a difference between an opticalenergy absorption rate of the detection target such as a tumor andoptical energy absorption rates of other tissues. By performing analysisprocessing on the detection signals, an optical characteristicdistribution, and especially, an optical-energy absorption densitydistribution are obtained. This information may be used for quantitativemeasurement of a specific substance included in the inspection targetsuch as glucose and hemoglobin included in blood, for example.Accordingly, the photoacoustic tomography may be utilized to specify aportion which includes a malignant tumor and growing new blood vessels.

Furthermore, Lihong V. Wang in “Tutorial on Photoacoustic Microscopy andComputed Tomography” (hereafter “Non Patent Literature 1”) discloses anexample of a case where a photoacoustic microscope is employed forphotoacoustic imaging (PAI). According to Non Patent Literature 1,ultrasonic waves obtained by irradiating an inspection target withpulsed light are received by a transducer which performs imaging.Furthermore, by changing a wavelength of the pulsed light, spectroscopiccharacteristics of the inspection target are imaged.

CITATION LIST Patent Literature

PTL 1 U.S. Pat. No. 5,840,023

Non Patent Literature

NPL 1 Lihong V. Wang “Tutorial on Photoacoustic Microscopy and ComputedTomography”, IEEE Journal of Selected Topics in Quantum Electronics,Vol. 14, No. 1, 171-179 (2008)

When the PAT technique is used, information on local light absorptioncan be obtained by measuring acoustic waves generated due to absorptionof light at a local inspection target portion. An initial acousticpressure P is represented by Expression (1) below using a distance rbetween a light irradiation point to the inspection target portion.

P(d)=Γμ_(a)(r)Φ(r)   Expression (1)

where Γ denotes a Gruneisen coefficient (heat-acoustic conversionefficiency), μ_(a)(r) denotes an absorption coefficient in a positioncorresponding to the distance r, and Φ(r) denotes a light intensity inthe position corresponding to the distance r. The Gruneisen coefficientΓ serving as an elastic characteristic value is obtained by dividing aproduct of a square of a thermal expansion coefficient β and a square ofan acoustic velocity c by a constant pressure specific heat Cp. Sincethe value Γ is substantially a constant value for the same livingtissues, when change of acoustic pressures P serving as amounts ofacoustic waves is measured in a time division manner, a product of thevalues μ_(a) and Φ, that is, an optical-energy absorption densitydistribution H is obtained. Furthermore, μ_(a)(r) is obtained bydividing the optical energy absorption density distribution H by thelight intensity Φ(r).

Here, a pulse laser used to generate photoacoustic waves may notgenerate pulsed light of a constant light quantity due to a fundamentalfunction thereof, and temporal output fluctuation occurs to some degree.Specifically, the light quantity fluctuation may reach 10% or more. Whenthe quantity of the pulsed light is varied, a light quantity Φ(r) in alocal region included in an inspection target is also varied. Asdescribed above, since the light quantity Φ(r) and the intensity P of aphotoacoustic wave have the proportional relationship, the photoacousticwaves similarly varies for individual laser pulses. Accordingly, whenthe optical energy absorption density H distribution and the absorptioncoefficient μ_(a) distribution are imaged, unevenness of intensityoccurs in a screen obtained after reconstruction and a quantitativeperformance of measurement may be deteriorated.

However, Patent Literature 1 above does not include a descriptionrelating to temporal output fluctuation of a light source. Furthermore,although Non Patent Literature 1 discloses a technique of correcting alight quantity using a sensor which is used to measure a pulsed-lightquantity, a measurement method, usage, and a correction target are notclearly described. Especially, since the description of Non PatentLiterature 1 has been made on the assumption that a photoacousticmicroscope is used, light attenuation in a depth direction which isimportant for measurement of a thick inspection target is not clearlydescribed.

The present invention has been made in view of the background techniqueand recognition of the problem described above. An object of the presentinvention is to provide a photoacoustic apparatus capable of reducing anadverse effect on an image caused when a quantity of light output from alight source varies with time.

SUMMARY OF INVENTION

To address the above problem, the present invention provides aphotoacoustic apparatus including a light source which irradiates aninspection target with pulsed light, a detector which detects acousticwaves generated in the inspection target due to interaction of thepulsed light with the inspection target, and outputs detections signalscorresponding to the detected acoustic waves, a light-quantitymeasurement unit which measures a quantity of light output from thelight source, and a signal processor which processes the detectionsignals output from the detector so as to obtain information on aninside of the inspection target. The signal processor includes a signalcorrection unit which corrects intensities of the detection signals inaccordance with a temporal change in the quantity of light measured bythe light-quantity measurement unit so that variations of theintensities of the detection signals are suppressed.

Further features of the present invention will become apparent topersons having ordinary skill in the art from the following descriptionof exemplary embodiments with reference to the attached drawings.

BRIEF DESCRIPTION OF DRAWINGS

FIG. 1 is a diagram schematically illustrating a configuration of aphotoacoustic apparatus according to a first embodiment of the presentinvention.

FIG. 2 is a diagram illustrating output fluctuation of laser pulses.

FIG. 3 is a flowchart illustrating an example of a process ofdetermining correction amounts of intensities of detection signalsaccording to the first embodiment of the present invention.

FIGS. 4A to 4C are diagrams illustrating arrangements of a photosensoraccording to the present invention.

FIG. 5 is a diagram schematically illustrating a configuration of aphotoacoustic apparatus according to a second embodiment of the presentinvention.

FIG. 6 is a flowchart illustrating an example of a process ofdetermining correction amounts of intensities of detection signalsaccording to the second embodiment of the present invention.

FIG. 7 is a diagram schematically illustrating a configuration of aphotoacoustic apparatus according to a third embodiment of the presentinvention.

DESCRIPTION OF EMBODIMENTS

Hereinafter, the present invention will be described with reference tothe accompanying drawings. Note that the same components are basicallydenoted by the same reference numerals and redundant descriptionsthereof are omitted.

First Embodiment: Photoacoustic Apparatus

First, a configuration of a photoacoustic apparatus according to thisembodiment will be described with reference to FIG. 1.

The photoacoustic apparatus of this embodiment corresponds to aphotoacoustic imaging apparatus which images information on an inside ofan inspection target. When the inspection target is a living body, thephotoacoustic apparatus enables imaging of information on the livingbody in order to perform diagnosis of a malignant tumor or a bloodvessel disease and follow-up of chemical treatment. The “information onan inside of an inspection target” in the present invention correspondsto information on a distribution of sources which generated acousticwaves in response to light irradiation, and includes information on adistribution of initial acoustic pressures in the living body,information on an optical energy absorption density distributionobtained from the information on a distribution of initial acousticpressures, and information on a density distribution of a substanceincluded in a living tissue obtained from the information on adistribution of initial acoustic pressures in the living body and theinformation on optical energy absorption density distribution obtainedfrom the information on a distribution of initial acoustic pressures.For example, the density distribution of a substance corresponds tooxygen saturation.

The photoacoustic apparatus of this embodiment includes a pulsed laser 2a, a detector 5, and a photosensor 8 a as a basic hard configuration.The pulsed laser 2 a is a light source used to irradiate the inspectiontarget with pulsed light. It should be noted that in place of the pulsedlaser 2 a, a different light source (e.g., a modulated light source orenergy beam) capable of generating pulses of light may be used.

An inspection target 3 such as a living body is fixed to plates 4 a and4 b which presses and fixes the inspection target 3 from both sides ofthe inspection target 3 where appropriate. Light emitted from the lightsource is guided to a surface of the plate 4 b by an optical system (notshown) including a lens, a mirror, and an optical fiber so that theinspection target is irradiated with the light. When part of lightenergy propagated through the inspection target 3 is absorbed by anoptical absorber such as blood vessels, the optical absorber generatesacoustic waves (typically, ultrasonic waves) due to thermal expansion.These acoustic waves may be referred to as “photoacoustic waves”. Thatis, a temperature of the optical absorber is increased due to absorptionof pulsed light, the increased temperature causes volume expansion, andaccordingly, photoacoustic waves are generated. Here, the duration(length) of a light pulse preferably corresponds to a degree in which aheat/stress sealing condition is satisfied so that absorption energy isefficiently sealed in the optical absorber. Typically, the duration of alight pulse may range from approximately 1 nanosecond to approximately0.2 seconds, but it is not limited thereto. Persons having ordinaryskill in the art may derive appropriate light pulse lengthscorresponding to the type of optical absorber which can provide aheat/stress sealing condition so that absorption energy is efficientlysealed in the optical absorber of interest.

A detector 5 used to detect acoustic waves detects the acoustic wavesgenerated in the inspection target and converts the acoustic waves intoanalog electric signals (detection signals). The detection signalsobtained from the detector correspond to the detected acoustic waves andfor this reason are referred to as “photoacoustic signals” whereappropriate.

A signal processor 15 which processes the photoacoustic signals so as toobtain information on an inside of the inspection target 3 includes areception amplifier 6, an A/D converter 7, a signal correction unit 11,an image reconstruction processing unit 12, and an optical attenuationcorrection unit 16 in this embodiment. The photoacoustic signalsobtained from the detector 5 are amplified by the reception amplifier 6and converted into digital photoacoustic signals by the A/D converter 7.The signal correction unit 11 which is one of the characteristiccomponents of this embodiment performs correction of intensities of thedigital signals. The image reconstruction processing unit 12 performscalculation processing on three-dimensional information, the opticalattenuation correction unit 16 performs correction on obtained voxeldata taking light attenuation in the inspection target intoconsideration. A resulting photoacoustic image of the inspection targetis displayed in an image display unit 13 where appropriate. Furthermore,all the components are controlled by a system controller 1. Here, the“photoacoustic image” is obtained by representing the obtainedinformation on the inside of the inspection target by a coordinate in athree-dimensional space and converting the information into luminanceinformation.

Next, characteristic portions of the first embodiment will be describedbelow. A quantity of light output from the laser 2 a is measured by thephotosensor 8 a serving as a light-quantity measurement device. When thequantity of light output from the laser 2 a varies with time, thisvariation is also measured by the photosensor 8 a. Then, the signalcorrection unit 11 corrects intensities of the photoacoustic signals soas to suppress variations of the intensities of the photoacousticsignals. That is, the variations of the intensities of the photoacousticsignals caused by the variation of the quantity of output light withtime (temporal change) can be reduced.

Light Source and Variation of Quantity of Light Output from Light Source

The laser light generated by the laser 2 a varies with respect to eachpulse. An example of light quantity variation is shown in FIG. 2. InFIG. 2, a temporal change of a measurement output obtained when a YAGlaser of approximately 5 W (500 mJ) generates pulsed light of 10 Hz for60 seconds is measured. According to FIG. 2, the output light quantityhaving light quantity variation of approximately 10% is recognized.

When the inspection target is a living body, the light source emitslight having a specific wavelength which is absorbed by a specificconstituent among constituents included in the living body. A pulselight source capable of generating pulsed light of 1 nanosecond order to0.2 nanoseconds order is preferably used as the light source. Although alaser is preferably used as the light source, a light-emitting diode maybe used instead of the laser. Examples of the laser include asolid-state laser, a gas laser, a dye laser, and a semiconductor laser.

Note that the variation of the output light quantity of the laser shownin FIG. 2 is supposed to be mainly caused by variation of a lightquantity of a flash lamp serving as a laser excitation light source.Therefore, when the flash lamp or a laser generated from the flash lampserving as the excitation light source is used as the light source ofthe present invention, an effect of the present invention is efficientlyobtained. However, as noted above, the light source of the presentinvention is not limited to these sources, and a semiconductor laser ora light-emitting diode which does not include a flash lamp may employthe present invention as long as the light source generates the lightquantity variation.

Note that, although an example of a case where a single light source isemployed is described in this embodiment, a plurality of light sourcesmay be used, as described below in reference to FIG. 5. When a pluralityof light sources are used, the light sources which oscillate in the samewavelength may be used in order to increase an intensity of lightemitted to the living body.

Alternatively, light source having different oscillation wavelengths maybe used in order to measure differences among optical characteristicvalue distributions depending on wavelengths. Note that, if pigments inwhich oscillation wavelengths can be changed or OPOs (Optical ParametricOscillators) is used as light sources, differences among opticalcharacteristic value distributions depending on wavelengths can bemeasured. A wavelength to be used is selected from a wavelength band ina range from 700 nm to 1100 nm which is merely absorbed in the livingbody. Note that, when an optical characteristic value distribution ofliving tissues comparatively in the vicinity of a surface of the livingbody is to be obtained, a wavelength is selected from a wavelength bandin a range from 400 nm to 1600 nm which is larger than the abovewavelength band.

The light emitted from the light source may be propagated using anoptical waveguide where appropriate. Although not shown in FIG. 1, anoptical fiber is preferably used as the optical waveguide. When anoptical fiber is used, a plurality of optical fibers may be used foreach light source so as to guide light to the surface of the livingbody. Alternatively, light beams emitted from a plurality of lightsources may be guided to a single optical fiber so that all the lightbeams are guided to the living body only using the single optical fiber.Furthermore, light may be guided by an optical member such as a mirrorwhich mainly reflects light or a lens which collects and enlarges lightand which changes a shape of the light. Any optical member may be usedas long as light emitted from a light source is encountered on a lightirradiation region included in the surface of the inspection target in adesired shape.

First Correction of Detection Signals

Correction of detection signals according to this embodiment will bedescribed in detail hereinafter.

A case where the inspection target is fixed on the plates as shown inFIG. 1, the region in which the laser 2 a irradiates with light is seton the surface of the inspection target in a two-dimensional manner, andthe light irradiation region is sufficiently larger than an imagingrange will be described as an example. A quantity of pulsed lightemitted onto the surface of the inspection target is represented by Φ₀.In the inspection target, light in portions farther than the surface isattenuated in an exponential manner due to absorption and scattering.That is, the following expression is obtained:

Φ(r)=Φ_(C)·exp(−μ_(eff) ·r)   Expression (2)

where μeff denotes an average effective attenuation coefficient of theinspection target. According to Expressions (2) and (1), the followingexpression is obtained.

P(r)=Γμ_(a)(d)Φ_(C)·exp(−μ_(eff) ·r)   Expression (3)

In the present invention, a problem arises in that the value Φ₀ varieswith respect to pulses. For example, when a first pulse has an outputlight amount Φ₀₁ and a second pulse has an output light amount Φ₀₂ whichis equal to 0.9Φ₀₁, an acoustic pressure P₂(r) of a photoacoustic wavegenerated by the second pulse is equal to 0.9P₁(r).

Therefore, since an image (μ_(a) distribution) of the inside of theinspection target generated from the first pulse and an image generatedfrom the second pulse have different luminance signals relative to theacoustic pressures, image reproducibility is not obtained. Accordingly,when the same portion is measured several times, information on theinside of the inspection target is misrecognized due to deterioration ofthe image reproducibility. Furthermore, when measurement is performedwhile the surface of the inspection target is scanned using a laser anda detector, a single image is generated using acoustic pressuresobtained in response to a plurality of pulses. In this case, unevennessof luminance occurs in the image due to the light quantity variationdescribed above, and this also causes misrecognition of the informationon the inside of the inspection target.

Therefore, in this embodiment, output light quantities Φ_(0n) of pulsesare measured using the photosensor 8 a. Then, intensities of detectionsignals of photoacoustic waves are corrected so that acoustic pressuresP_(n)(r) are supposed to be normally obtained in accordance with areference light quantity such as a constant initial light quantity Φ₀.In the foregoing example, assuming that the acoustic pressure P₁(r) isused as a reference and an intensity corresponding to 1/0.9 an acousticpressure P₂(r) is obtained, detection signals are corrected. By this,even when outputs of the light source vary with time, influence cased bythe variation can be reduced and information on positions of soundsources and acoustic pressures can be obtained.

Note that, an inverse number of a ratio of the output light quantity Φ₀₂of the second pulse to the output light quantity Φ₀ of the first pulse,that is, Φ₀₁/Φ₀₂ is referred to as a “correction coefficient” in thisspecification. Furthermore, the correction of detection signalsdescribed above may be performed on analog signals and digital signals.However, in this embodiment, the correction is performed on amountsconverted into digital signals by the A/D converter 7. When digitalsignals are to be corrected, since the A/D converter 7 outputs values ofthe acoustic pressures P(r) for individual sampling frequencies, thecorrection is performed by multiplying a digital signal representing anacoustic pressure P(r) corresponding to a certain pulse by a correctioncoefficient of the pulse.

Hereinafter, further details are described. In this embodiment, afterthe photosensor 8 a detects a pulse light quantity of the laser 2 a foreach pulse, the pulse light quantity is stored in a light-quantitymemory 9 a. Such a memory used to store an output light quantity ispreferably provided in terms of reliability of signal processing. Acorrection-amount determination unit 10 reads data indicative of atemporal change in the output light quantity stored in thelight-quantity memory 9 a, and determines correction amounts (correctioncoefficients) for the detection signals. In accordance with thedetermined correction amounts, the signal correction unit 11 correctsintensities of the detection signals.

FIG. 3 is a processing flow of correction amount calculation. Thecorrection-amount determination unit 10 reads data from thelight-quantity memory 9 a (in step S301). In accordance with lightquantities of pulses obtained from the light-quantity memory 9 a,correction coefficients for the pulses are calculated (in step S302). Alight quantity measured in advance is used as a reference value for thecorrection coefficients. In this specification, a set of correctioncoefficients of a plurality of pulses is referred to as a “correctionamount table”. Then, the correction amount table is transmitted to thesignal correction unit 11 (in step S303) where obtained photoacousticsignals are calculated using the correction amount table. That is,digital signals of acoustic pressures P(d) obtained for individualsampling frequencies are multiplied by the correction coefficients.

Image Reconstruction and Optical Attenuation Correction

The image reconstruction processing unit 12 performs imagereconstruction on the digital signals which have been corrected asdescribed above. The image reconstruction of the PAT is performed toobtain a distribution P₀(r) of initial acoustic pressures generated inthe inspection target from acoustic pressures P_(d)(r_(d), t) receivedby the detector, and is referred to as an “inverse problem” in themathematical field. A universal back projection (UBP) methodrepresentatively used as the image reconstruction method of the PAT hasbeen described in Physical Review E 71, 016706 (2005) and Review ofScientific Instruments, 77, 042201 (2006).

As described above, the distribution of initial acoustic pressuresserving as the information on the inside of the inspection target and aproduct of the value μ_(a) and the value Φ, that is, an optical energyabsorption density distribution H are obtained. Assuming that the valueΦ is a constant value, when a value H is divided by the value Φ, adistribution of absorption coefficients μ_(a)(r) in the inspectiontarget is obtained. However, since a quantity of light emitted to alocal region of the inspection target attenuates in an exponentialmanner as described above, when two tissues have the same absorptioncoefficient, an acoustic pressure of an acoustic wave generated from oneof the tissues which is located farther from the surface of theinspection target is smaller than that of the other tissue which islocated nearer the surface of the inspection target. Therefore, in orderto obtain a reliable absorption coefficient distribution, such influenceof light attenuation is preferably corrected. This correction isreferred to as “light attenuation correction” in this specification.

Specifically, the optical attenuation correction unit 16 performs aprocess of dividing voxel data items representing the absorption densitydistribution H of optical energy output from the image reconstructionprocessing unit 12 by corresponding light quantities in positions of thevoxels. The light quantities in the positions of the correspondingvoxels are calculated by Expression (2) above.

With this configuration, a reliable absorption coefficient distributionin the inspection target can be imaged taking the influence of theoptical attenuation into consideration.

Example of First Signal Correction

Note that although a case where correction for light quantity variationswith respect to pulses is performed on data which corresponds to digitalsignals obtained by the A/D converter 7 and has not been subjected tothe image reconstruction processing is described in this embodiment, thepresent invention is not limited to this. The correction may beperformed on voxel data which has been subjected to the imagereconstruction processing. That is, correction of photoacoustic signalsmay be similarly performed by inputting the correction coefficientscalculated by the correction-amount determination unit 10 to the opticalattenuation correction unit 16 so that correction calculation isperformed. Furthermore, the correction may be performed on analog datawhich has not been subjected to the A/D conversion. In this case, amethod for controlling a gain of the reception amplifier 6 using anoutput from the correction-amount determination unit 10 may be employed.That is, the “detection signals” in this specification includes analogsignals, digital signals obtained through the A/D conversion, andluminance data obtained by performing the image reconstruction on thedigital data.

Furthermore, if a light quantity distribution in the inspection targetobtained when light is emitted can be set, when light is emitted fromopposite sides of the plate 4 or when light is emitted from variousdirections, the correction of photoacoustic signals can be similarlyperformed.

Moreover, although the photoacoustic signals are obtained in a state inwhich the detector 5 and the laser 2 a are fixed in the foregoingembodiment, even when photoacoustic signals are obtained while scanningis performed using the detector 5 and the laser 2 a, the correction ofphotoacoustic signals can be similarly performed by obtaininglight-quantity measurement data in various scanning positions.

In addition, the laser pulse 2 a to be used is a laser beam having acertain width. When spatial unevenness of an intensity of a section ofthe laser beam occurs, the correction of photoacoustic signals can besimilarly performed by calculating correction light quantities in athree-dimensional space taking the light quantity distribution intoconsideration.

Detailed Descriptions of Configurations

The detector (probe) 5 detects acoustic waves such as sonic waves andultrasonic waves and converts the acoustic waves into electric signals.Any acoustic wave detector such as a transducer utilizing piezoelectricphenomenon, a transducer utilizing optical resonance, or a transducerutilizing change of capacitance may be used as long as the acoustic wavedetector can detect acoustic wave signals. The detector 5 in thisembodiment is preferably an array type detector having a plurality oftransducer elements. When the transducer elements arranged in atwo-dimensional manner are used, acoustic waves are simultaneouslydetected in a plurality of portions. Accordingly, a period of timerequired for the detection can be reduced and influence of vibration ofthe inspection target can be reduced. Furthermore, an acoustic impedancematching agent such as gel or water is preferably used between thedetector 5 and the plate 4 b and between the plate 4 b and theinspection target 3 so as to suppress reflection of acoustic waves.

Examples of a typical light-quantity measurement device include aphotosensor as typified by a photodiode and a pyroelectric sensor. Whena one-dimensional or a two-dimensional photosensor array is required, aCCD image sensor, a CMOS image sensor, a light dependent resistor (LDR),or the like may be used to obtain a similar effect.

A preferable arrangement of the photosensor 8 a serving as thelight-quantity measurement device will be described with reference toFIGS. 4A to 4C. A reference numeral 18 denotes a reflection mirror and areference numeral 19 denotes a laser beam of pulsed light.

FIG. 4A shows a case where light leaked from a reflection mirrordisposed in the optical system is detected before light reaches theplate 4 b. As shown in FIG. 4A, since the photosensor 8 a is disposedafter the reflection mirror, part of the light emitted from the lightsource can be detected. If a rate of the leakage light is known inadvance, variation of quantities of light emitted from the light sourcecan be calculated.

FIG. 4B shows a case where part of light reflected by the plate 4 b isdetected. As shown in FIG. 4B, the photosensor 8 a may be disposed inthe vicinity of the plate 4 b.

FIG. 4C shows a case where part of light which has been propagatedinside the plate 4 b is detected. As shown in FIG. 4C, the photosensor 8a may be disposed at an end portion of the plate 4 b. Especially, whenlight is obliquely entered relative to the plate 4 b, light propagatedinside the plate 4 b is increased, which is preferable.

As a memory, a memory included in a PC or a control board may beemployed. However, a similar effect can be obtained when a memoryattached to a photosensor unit is used or a hard disk is used as long asa speed higher than a laser pulse cycle is ensured.

FIRST EXAMPLE

Hereinafter, as a first example, a case where the photoacousticapparatus according to the present invention is employed in a breastexamination will be described in detail. In the breast examination ofthis example, breast compression similar to that generally performed inX-ray mammography is performed. That is, in the breast, photoacousticsignals within a depth of 4 cm which is an average thickness of thebreast compression should be obtained.

In this embodiment, as the light source, a Q switch YAG laser which hasa wavelength of 1064 nm, which is driven in 10 Hz, which has a pulsewidth of 5 nanoseconds, and which has an output per pulse of 1.6 J isused. Under this condition, since a human body allows to be irradiatedwith laser light having an intensity of 100 mJ/cm2 or smaller accordingto JIS, an illumination optical system which enlarges emitted laserlight to square 4 cm on a side is designed.

Then, it is assumed that a range in which photoacoustic signals aregenerated in response to light emitted from both sides of the breastwhile the breast is compressed has a depth of 4 cm and a width of 4 cm.Furthermore, in order to obtain the photoacoustic signals within thisrange, an ultrasonic transducer has 4 cm on a side. Furthermore, atwo-dimensional probe having 400 elements is configured while an elementpitch is set to 2 mm. In addition, a frequency of 1 MHz is used. A PINphotodiode S5973 manufactured by Hamamatsu Photonics K.K. is used as aphotosensor.

When photoacoustic signals are to be obtained under the conditiondescribed above, a quantity of irradiated light obtained at a time oflaser irradiation is normally stored in a light-quantity memory.Correction coefficients for pulses are calculated using the maximumvalue of a measured light-quantity variation of 1. Correction ofdetection signals is performed in accordance with the correction methoddescribed with reference to the configuration shown in FIG. 1. Aphotoacoustic image generated through image reconstruction is stored asvolume data and displayed in a screen.

Although unevenness of an intensity of the photoacoustic image can beimproved using this method, since reproducibility of the photoacousticsignals based on electric noise is approximately 2% to approximately 3%and unevenness of distribution of irradiated light is approximately 2%,unevenness of an image remains in a similar degree. However, when thismethod is employed, the unevenness of image of approximately 8% toapproximately 10% can be reduced to approximately 3% to 4%.

Note that distribution of irradiated light can be measured byadditionally disposing a CCD sensor or the like in an optical path. Thereproducibility of the photoacoustic signals can be measured byoperating this system in a state in which laser irradiation is notperformed. The image unevenness is defined to be three times standarddeviation of luminance value variation at the same pixel obtained whenimage capturing is performed a plurality of times.

Note that, although the case where the photoacoustic apparatus is usedfor the breast examination is described in detail in this embodiment,similar effects are obtained when the other portions of the human bodyand inspection bodies other than a human body are measured by similarprocessing.

Second Embodiment

In the first embodiment, the laser light is emitted only from one side.In a second embodiment, a correction method employed when laser light isemitted from opposite sides of a plate 4 will be described. FIG. 5 showsan example of a photoacoustic apparatus according to this embodiment.Irradiation of laser pulses, light-quantity data, and photoacousticsignals are obtained similarly to the first embodiment. This embodimentis different from the first embodiment in that the laser light isemitted from opposite sides, that is, from lasers 2 a and 2 b andoutputs of the lasers 2 a and 2 b are detected by photosensors 8 a and 8b, respectively. It should be noted that although the laser sources 2 aand 2 b and corresponding photosensors 8 a and 8 b are shown as separateelements for ease of illustration, the lasers sources can be part of asingle laser source and the photosensors can be part of a singlephotosensor array. Accordingly, it can be said that a light source mayinclude a plurality of light sources, and that a light-quantitymeasurement unit may include a plurality of light-quantity measurementunits. Detected light quantities are stored in light-quantity memories 9a and 9 b and transmitted to correction-amount determination units 10 aand 10 b. Then, two correction coefficients are calculated using amethod similar to that of the first embodiment, and the correctioncoefficients are transmitted to a signal correction unit 11.

Processes performed by the correction-amount determination units 10 aand 10 b and a processes performed by a signal correction unit 11 willbe described in detail with reference to FIG. 6. Correction coefficientsfor light quantities of lasers obtained from the light-quantity memories9 a and 9 b (in step S601) are calculated by setting the maximum valueof light-quantity variations measured in advance to 1 (in step S602).Then, relative attenuation amounts in a depth direction are calculatedusing standardized light quantities and the coefficients so that twocorrection-amount tables are generated using two light-quantity dataitems (in step S603). The correction-amount tables in the depthdirection are added to each other relative to the same depth so that asynthesized correction-amount table is generated (in step S604).

That is, acoustic pressures obtained in accordance with light emittedfrom one side of the plate 4 is represented similarly to Expression (3)described above.

P(r)=Γμ_(a)(r)Φ_(CA)·exp(−μ_(eff) ·r)   Expression (3)

However, an acoustic pressure obtained in accordance with light emittedfrom the other side is represented by the following expression.

P(r)=Γμ_(a)(r)Φ_(CB)·exp(−μ_(eff)·(D−r))   Expression (4)

Here, D denotes a distance between the compression plates 4 a and 4 b,and Φ_(CA) denotes an initial light quantity obtained after pulsed lightemitted from the laser 2 a is multiplied by a corresponding one of thecorrection coefficients of the light quantity variations. Furthermore,Φ_(CB) denotes an initial light quantity obtained after pulsed lightemitted from the laser 2 b is multiplied by a corresponding one of thecorrection coefficients of the light quantity variations. Each of thecorrection-amount tables is obtained by quantifying the light quantityin the above expression and light attenuation in accordance with asampling frequency and adding them with each other, and therefore, isrepresented by the following expression.

C(r)=1/Φ_(CA)·(exp(−μ_(eff) ·r)+Φ_(0B)exp (−μ_(eff)·(D−r))))  Expression (5)

Here, C(r) denotes values of the correction-amount tables, Φ_(0A),Φ_(0B), r, D, and μ_(eff) can be obtained since they are known inadvance. Then, synthesized correction-amount table C(d) is multiplied byobtained image reconstruction data (in step S605). At this time, thecorrection-amount tables are functions in the depth direction (astraight-line distance from a surface of an inspection target). On theother hand, the image reconstruction data is three-dimensional data butmultiplication is performed only in the depth direction and a certainprocess is performed in a height and width direction (in an in-planedirection of the surface of the inspection target). Thereafter, aphotoacoustic image is stored as volume data and displayed in a screen.With this method, a process of correcting digital data which has beensubjected to the image reconstruction taking the variations ofquantities of light supplied from a light source into consideration anda process of correcting digital data which has been subjected to theimage reconstruction taking light attenuation in the depth directioninto consideration are collectively performed. In this case, detectionsignals may be acoustic pressure signals which have been converted intoluminance signals.

According to this embodiment, as with the first embodiment, even whenthe light is emitted from opposite sides of the plate 4, imageunevenness can be improved.

Third Embodiment

In the first and second embodiments, the intensities of thephotoacoustic signals are corrected assuming that the surface of theinspection target is irradiated with the constant light quantity Φ₀irrespective of portions. In a third embodiment, a correction methodemployed when intensity distribution of initial light quantities isgenerated on a surface to which a laser is encountered (a surface of aninspection target) will be described.

FIG. 7 shows an example of a photoacoustic apparatus of this embodiment.Emission of laser pulses and obtainment of light-quantity data andphotoacoustic signals are performed similarly to the second embodiment.Laser to be emitted to an inspection target 3 is enlarged to square 4 cmon a side which is the same as a detector 5 and is emitted. Intensitydistribution is included in a plane. This is especially observed when amultimode laser is used. The in-plane intensity distribution is measuredin advance and stored in light-quantity distribution memories 14 a and14 b.

Note that a correction amount used for correction is obtained byreflecting the light intensity distribution. That is, the correctionamount corresponds to a function of the initial light quantity and anattenuation coefficient obtained by multiplying the light intensitydistribution, a Gruneisen coefficient, an absorption coefficient, and acorrection coefficient, and is calculated using light propagationsimulation since the light intensity distribution is not analyticallyobtained. A light-quantity distribution in a three-dimensional directionis obtained through the calculation, and Expression (3) is replaced bythe following expression:

P(r)=Γμ_(a)(d)Φ_(C)(x, y, r, t)·exp(−μ_(eff) ·r)   Expression (6)

where a light quantity Φ₀(x, y, r, t) corresponds to a function of aspace (x, y, r) distribution and each pulse oscillated every time periodt. This light quantity Φ₀ is calculated through the simulation, andafter coefficients are multiplied, inversed numbers are obtained wherebycorrection coefficients in portions in the three-dimensional space areobtained.

The correction-amount calculation of this embodiment is excellent inthat signal correction is performed taking, in addition tolight-quantity variations with time, spatial irradiation light quantitydistribution in a surface of the inspection target into consideration.Reproducibility of the photoacoustic signals is the same as that of thefirst embodiment. When a photoacoustic image is obtained and correctedtaking these factors into consideration, unevenness of an intensity ofthe photoacoustic image which is 8% to 10% in a state in which thelight-quantity distribution correction has not been performed can bereduced to approximately 3%, that is, reduced to a degree substantiallythe same as the reproducibility of the photoacoustic signals.

Fourth Embodiment

In the first to third embodiments, the photoacoustic signals areobtained while the detector 5 and the laser 2 a are fixed. In a fourthembodiment, a case where photoacoustic signals are obtained while adetector 5 and a laser 2 a are moved along a plate 4 for scanning.

A system configuration is shown in FIGS. 4A to 4C. However, in thisembodiment, a movement mechanism which moves the laser 2 a, a laser 2 b,and the detector 5 relative to an inspection target is provided. Notethat as long as a light incidence portion of the inspection target inwhich light is incident from a light source is scanned, the lasersthemselves are not required to be moved for scanning. In this case, alight-quantity variation generated during the scanning which is nottaken into consideration in the first to third embodiments should becorrected.

Assuming that breast is scanned using the light source and theultrasonic transducer described above, a scanning region corresponds toa range of 20 cm×20 cm and a stripe width is 4 cm, and accordingly, astripe pattern of 4 cm×20 cm is formed five times. Furthermore, astep-and-repeat method, that is, a method for repeating move and stop ofthe transducer and performing laser irradiation while the transducer isstopped is employed in the scanning performed by the transducer, and inthis way, photoacoustic signals are obtained. On the other hand, at atime of laser irradiation, an irradiation light quantity is normallystored in a light-quantity memory.

Standardization of light quantities, calculation processing, andcorrection of photoacoustic signals are performed similarly to thesecond embodiment. However, corrected photoacoustic signals aretemporarily stored in a memory until scanning is terminated. Then, afterthe scanning is completely terminated, image reconstruction is performedusing the corrected photoacoustic signals, and a generated photoacousticimage is stored as volume data and displayed in a screen.

Intensity unevenness of a photoacoustic image can be improved throughthis method. Reproducibility of a photoacoustic signals corresponds toapproximately 2% to approximately 3% while an S/N ratio is increasedfour or five times as an effect of averaging of the photoacousticsignals by the scanning. Taking such influence into consideration, imageunevenness corresponding to approximately 8% to approximately 10% in astate in which the light-quantity correction has not been performed inconventional scanning is reduced to 1% or less.

Fifth Embodiment

Furthermore, the present invention may be realized by performing thefollowing processing. Specifically, software (a program) which realizesthe functions of the foregoing embodiments is supplied to a system or anapparatus through a network or various storage media, and a computer (aCPU, an MPU, or the like) included in the system of the apparatus readsand execute the program.

According to the present invention, a photoacoustic apparatus whichincludes a light-quantity measurement unit and which correctsintensities of photoacoustic signals taking a temporal change of anoutput light quantity measured by the light-quantity measurement unitinto consideration so that adverse effect of the output fluctuation onan image becomes negligible even when temporal output fluctuation oflight output from a light source occurs can be provided.

While the present invention has been described with reference toexemplary embodiments, it is to be understood that the invention is notlimited to the disclosed exemplary embodiments. The scope of thefollowing claims is to be accorded the broadest interpretation so as toencompass all such modifications and equivalent structures andfunctions.

REFERENCE SIGNS LIST

-   1 SYSTEM CONTROLLER-   2 a, 2 b LASER-   3 INSPECTION TARGET-   4 a, 4 b PLATE-   5 DETECTOR-   6 RECEPTION AMPLIFIER-   7 ANALOG-DIGITAL CONVERTER-   8 a, 8 b PHOTOSENSOR-   9 a, 9 b LIGHT-QUANTITY MEMORY-   10 CORRECTION-AMOUNT CALCULATION UNIT-   11 SIGNAL CORRECTION UNIT-   12 IMAGE RECONSTRUCTION PROCESSOR-   15 SIGNAL PROCESSOR-   16 LIGHT ATTENUATION CORRECTION UNIT

What is claimed is:
 1. A photoacoustic apparatus comprising: a lightsource which irradiates an inspection target with pulsed light; adetector which detects acoustic waves generated in the inspection targetdue to interaction of the pulsed light with the inspection target, andoutputs detection signals corresponding to the detected acoustic waves;a light-quantity measurement unit which measures a quantity of lightoutput from the light source; and a signal processor which processes thedetection signals output by the detector so as to obtain information onan inside of the inspection target, wherein the signal processorincludes a signal correction unit which corrects intensities of thedetection signals in accordance with a temporal change in the quantityof light measured by the light-quantity measurement unit so thatvariations in the intensities of the detection signals are suppressed.